Method for controlling an electrosurgical generator

ABSTRACT

A microwave ablation system includes a generator including a first energy source, a second energy source and a diplexer, the diplexer multiplexes a first energy from the first energy source and a second energy from the second energy source. The system also includes a cable including a center conductor and an outer sheath where the multiplexed energy is transmitted through the center conductor. In addition an antenna is provided that is operable to receive the multiplexed energy from the center conductor and to deliver the multiplexed energy to a region of tissue. The outer sheath acts as a return path of the second energy to the second energy source. A sensor is also provided that measures at least one parameter of the second energy generated by the second energy source and the second energy returned from the region of tissue.

CROSS REFERENCE TO RELATED APPLICATIONS

This application is a divisional of U.S. patent application Ser. No.15/354,595, filed Nov. 17, 2016, which is a continuation of U.S.application Ser. No. 13/943,452, filed Jul. 16, 2013, now U.S. Pat. No.9,504,524, which is a continuation of U.S. application Ser. No.13/568,679, filed on Aug. 7, 2012, now U.S. Pat. No. 8,486,057, which isa divisional of U.S. application Ser. No. 12/468,718, filed on May 19,2009, now U.S. Pat. No. 8,246,615.

INTRODUCTION

The present disclosure relates generally to microwave ablationprocedures that utilize microwave surgical devices having a microwaveantenna which may be inserted directly into tissue for diagnosis andtreatment of diseases. More particularly, the present disclosure isdirected to measuring tissue impedance during a microwave ablationprocedure.

BACKGROUND

In the treatment of diseases such as cancer, certain types of cancercells have been found to denature at elevated temperatures (which areslightly lower than temperatures normally injurious to healthy cells.)These types of treatments, known generally as hyperthermia therapy,typically utilize electromagnetic radiation to heat diseased cells totemperatures above 41° C., while maintaining adjacent healthy cells atlower temperatures where irreversible cell destruction will not occur.Other procedures utilizing electromagnetic radiation to heat tissue alsoinclude ablation and coagulation of the tissue. Such microwave ablationprocedures, e.g., such as those performed for menorrhagia, are typicallydone to ablate and coagulate the targeted tissue to denature or kill thetissue. Many procedures and types of devices utilizing electromagneticradiation therapy are known in the art. Such microwave therapy istypically used in the treatment of tissue and organs such as theprostate, heart, liver, lung, kidney, and breast.

One non-invasive procedure generally involves the treatment of tissue(e.g., a tumor) underlying the skin via the use of microwave energy. Themicrowave energy is able to non-invasively penetrate the skin to reachthe underlying tissue. However, this non-invasive procedure may resultin the unwanted heating of healthy tissue. Thus, the non-invasive use ofmicrowave energy requires a great deal of control.

Presently, there are several types of microwave probes in use, e.g.,monopole, dipole, and helical. One type is a monopole antenna probe,which consists of a single, elongated microwave conductor exposed at theend of the probe. The probe is typically surrounded by a dielectricsleeve. The second type of microwave probe commonly used is a dipoleantenna, which consists of a coaxial construction having an innerconductor and an outer conductor with a dielectric junction separating aportion of the inner conductor. The inner conductor may be coupled to aportion corresponding to a first dipole radiating portion, and a portionof the outer conductor may be coupled to a second dipole radiatingportion. The dipole radiating portions may be configured such that oneradiating portion is located proximally of the dielectric junction, andthe other portion is located distally of the dielectric junction. In themonopole and dipole antenna probe, microwave energy generally radiatesperpendicularly from the axis of the conductor.

The typical microwave antenna has a long, thin inner conductor thatextends along the axis of the probe and is surrounded by a dielectricmaterial and is further surrounded by an outer conductor around thedielectric material such that the outer conductor also extends along theaxis of the probe. In another variation of the probe that provides foreffective outward radiation of energy or heating, a portion or portionsof the outer conductor can be selectively removed. This type ofconstruction is typically referred to as a “leaky waveguide” or “leakycoaxial” antenna. Another variation on the microwave probe involveshaving the tip formed in a uniform spiral pattern, such as a helix, toprovide the necessary configuration for effective radiation. Thisvariation can be used to direct energy in a particular direction, e.g.,perpendicular to the axis, in a forward direction (i.e., towards thedistal end of the antenna), or combinations thereof.

Invasive procedures and devices have been developed in which a microwaveantenna probe may be either inserted directly into a point of treatmentvia a normal body orifice or percutaneously inserted. Such invasiveprocedures and devices potentially provide better temperature control ofthe tissue being treated. Because of the small difference between thetemperature required for denaturing malignant cells and the temperatureinjurious to healthy cells, a known heating pattern and predictabletemperature control is important so that heating is confined to thetissue to be treated. For instance, hyperthermia treatment at thethreshold temperature of about 41.5° C. generally has little effect onmost malignant growth of cells. However, at slightly elevatedtemperatures above the approximate range of 43° C. to 45° C., thermaldamage to most types of normal cells is routinely observed. Accordingly,great care must be taken not to exceed these temperatures in healthytissue.

In the case of tissue ablation, a high radio frequency electricalcurrent in the range of about 500 mHz to about 10 gHz is applied to atargeted tissue site to create an ablation volume, which may have aparticular size and shape. Ablation volume is correlated to antennadesign, antenna performance, antenna impedance and tissue impedance. Theparticular type of tissue ablation procedure may dictate a particularablation volume in order to achieve a desired surgical outcome. By wayof example, and without limitation, a spinal ablation procedure may callfor a longer, narrower ablation volume, whereas in a prostate ablationprocedure, a more spherical ablation volume may be required.

Microwave ablation devices utilize thermocouples to determine when anablation is complete. When the thermocouple reaches thresholdtemperature the ablation procedure is completed. Tissue impedance canalso be used to determine when the ablation procedure is completed.Because ablated tissue blocks electrical signals due to non-conductivedesiccated tissue, the tissue impedance can determine when the ablationprocedure is completed. During application of energy, the current andvoltage applied to the tissue can be measured and used to calculateimpedance and the calculated impedance is stored. Based upon a functionof the impedance it is determined whether the ablation procedure iscomplete.

During an ablation procedure, if only one antenna is used, there is noeasy way to determine a change in tissue impedance. The inability todetermine the change in tissue impedance is due to losses in the coaxialcable used to deliver energy to the antenna. The coaxial cable can makeit difficult to measure any reflection from the antenna that could beused to determine the tissue impedance.

Additionally, antennas may use a coolant to provide improved ablationvolume and shape. Any suitable medium may be used as a coolant such asdeionized water, sterilized water, or saline. The coolant may havedielectric properties which may provide improved impedance matchingbetween an antenna probe and tissue. Impedance matching is the practiceof setting the probe impedance to the tissue impedance in order tomaximize the power transfer and minimize reflections from the load. Dueto the minimized reflections, if a water or dielectric buffer cooledantenna is used, the change in tissue impedance may be immeasurable.

SUMMARY

The present disclosure provides a microwave ablation system. Themicrowave ablation includes a generator including a first energy source,a second energy source and a diplexer, the diplexer operable tomultiplex a first energy from the first energy source and a secondenergy from the second energy source. A cable is also provided thatincludes a center conductor and an outer sheath. The multiplexed energyis transmitted through the center conductor. Also, an antenna operableto receive the multiplexed energy from the center conductor and todeliver the multiplexed energy to a region of tissue is provided. Theouter sheath acts as a return path of the second energy to the secondenergy source. A sensor is also provided that measures at least oneparameter of the second energy generated by the second energy source andthe second energy returned from the region of tissue.

The present disclosure also provides another microwave ablation system.The microwave ablation system includes a generator including a firstenergy source, a second energy source and a diplexer, the diplexeroperable to multiplex a first energy from the first energy source and asecond energy from the second energy source. A cable is also providedthat includes a center conductor and an outer sheath. The multiplexedenergy is transmitted through the center conductor. Also, an antennaoperable to receive the multiplexed energy from the center conductor andto deliver the multiplexed energy to a region of tissue is provided.Additionally, a return pad is provided that is operable to receive thesecond energy outputted from the antenna. The return pad transmits thesecond energy to the second energy source. A sensor is also providedthat measures at least one parameter of said second energy generated bysaid second energy source and the second energy returned from saidreturn pad.

The present disclosure also provides a method of ablating tissue usingmicrowave energy. The method includes generating microwave energy,generating radio frequency (RF) energy, multiplexing the microwaveenergy and the RF energy and outputting the multiplexed energy to atissue region. RF energy is returned from the tissue region and at leastone parameter of the generated RF energy and the RF energy returned fromsaid tissue region is measured. Based on the measured parameter thelevel of microwave energy that is generated is controlled.

BRIEF DESCRIPTION OF THE DRAWINGS

The above and other aspects, features, and advantages of the presentdisclosure will become more apparent in light of the following detaileddescription when taken in conjunction with the accompanying drawings inwhich:

FIG. 1 shows a representative diagram of a variation of a microwaveantenna assembly in accordance with an embodiment of the presentdisclosure;

FIG. 2 shows a cross-sectional view of a representative variation of adistal end of microwave antenna assembly in accordance with anembodiment of the present disclosure;

FIG. 3 shows a cross-sectional view of a representative variation of aproximal end of microwave antenna assembly in accordance with anembodiment of the present disclosure;

FIGS. 4A-4D show perspective views of the distal portion of a microwaveantenna in various stages of assembly in accordance with an embodimentof the present disclosure;

FIG. 5 is a schematic diagram of a microwave ablation system with abipolar RF energy source according to an embodiment of the presentdisclosure;

FIG. 6 is a diagram of a bipolar RF return path according to anembodiment of the present disclosure;

FIG. 7 is a schematic diagram of a microwave ablation system with amonopolar RF energy source according to an embodiment of the presentdisclosure; and

FIG. 8 is a diagram of a monopolar RF return path according to anembodiment of the present disclosure.

DETAILED DESCRIPTION

Particular embodiments of the present disclosure are describedhereinbelow with reference to the accompanying drawings; however, it isto be understood that the disclosed embodiments are merely exemplary ofthe disclosure and may be embodied in various forms. Well-knownfunctions or constructions are not described in detail to avoidobscuring the present disclosure in unnecessary detail. Therefore,specific structural and functional details disclosed herein are not tobe interpreted as limiting, but merely as a basis for the claims and asa representative basis for teaching one skilled in the art to variouslyemploy the present disclosure in virtually any appropriately detailedstructure. Like reference numerals may refer to similar or identicalelements throughout the description of the figures.

Electromagnetic energy is generally classified by increasing energy ordecreasing wavelength into radio waves, microwaves, infrared, visiblelight, ultraviolet, X-rays and gamma-rays. As used herein, the term“microwave” generally refers to electromagnetic waves in the frequencyrange of 300 megahertz (MHz) (3×108 cycles/second) to 300 gigahertz(GHz) (3×1011 cycles/second). As used herein, the term “RF” generallyrefers to electromagnetic waves having a lower frequency thanmicrowaves. The phrase “ablation procedure” generally refers to anyablation procedure, such as microwave ablation or microwave ablationassisted resection. The phrase “transmission line” generally refers toany transmission medium that can be used for the propagation of signalsfrom one point to another.

FIG. 1 shows an embodiment of a microwave antenna assembly 100 inaccordance with one embodiment of the present disclosure. Antennaassembly 100 includes a radiating portion 12 that is connected byfeedline 110 (or shaft) via cable 15 to connector 16, which may furtherconnect the assembly 10 to a power generating source 28, e.g., amicrowave or RF electrosurgical generator. Assembly 100, as shown, is adipole microwave antenna assembly, but other antenna assemblies, e.g.,monopole or leaky wave antenna assemblies, may also utilize theprinciples set forth herein. Distal radiating portion 105 of radiatingportion 12 includes a tapered end 120 which terminates at a tip 123 toallow for insertion into tissue with minimal resistance. It is to beunderstood, however, that tapered end 120 may include other shapes, suchas without limitation, a tip 123 that is rounded, flat, square,hexagonal, or cylindroconical.

An insulating puck 130 is disposed between distal radiating portion 105and proximal radiating portion 140. Puck 130 may be formed from anysuitable elastomeric or ceramic dielectric material by any suitableprocess. In embodiments, the puck 130 is formed by overmolding frompolyether block amide, which is available under the tradename PEBAX®from Arkema of Puteaux, France; polyetherimide, available under thetradename ULTEM® from Sabic Innovative Plastics IP B.V. of Bergen OpZoom, Netherlands; polyimide-based polymer available under the tradenameVESPEL® from E.I. Du Pont De Nemours and Company of Wilmington, Del. Asbest illustrated in FIG. 2, puck 130 includes coolant inflow port 131and coolant outflow port 133 to respectively facilitate the flow ofcoolant into, and out of, coolant chamber 148 of trocar 122 as furtherdescribed hereinbelow.

With reference now to FIGS. 2, 3, and 4A-4D, distal radiating portion105 includes a trocar 122 having a generally cylindroconical shape.Proximal radiating portion 140 includes a proximal antenna member 128having a generally cylindrical shape. Additionally or alternatively,proximal antenna member 128 may have a generally square or hexagonalshape. Trocar 122 and proximal antenna member 128 may be formed from avariety of biocompatible heat resistant conductive materials suitablefor penetrating tissue, such as without limitation, stainless steel.Antenna assembly 110 includes a coaxial transmission line 138 having, incoaxial disposition, an inner coaxial conductor 150, an intermediatecoaxial dielectric 132, and an outer coaxial conductor 134. Nominally,coaxial transmission line 138 has an impedance of about 50 ohms. Innercoaxial conductor 150 and outer coaxial conductor 134 may be formed fromany suitable electrically conductive material. In some embodiments,inner coaxial conductor 150 is formed from stainless steel and outercoaxial conductor 132 is formed from copper. Coaxial dielectric 132 maybe formed from any suitable dielectric material, including withoutlimitation, polyethylene terephthalate, polyimide, orpolytetrafluoroethylene (PTFE) (e.g., available under the tradenameTEFLON®, from E. I. du Pont de Nemours and Company of Wilmington, Del.,United States). Inner coaxial conductor 150 may be electrically coupledto trocar 122 and outer coaxial conductor 134 may be electricallycoupled to proximal antenna member 128.

A longitudinal opening 146 is defined within trocar 122 and opens to aproximal end thereof, and defines a cooling chamber 148 and a threadedsection 145 within trocar 122. Cooling chamber 148 may have a generallycylindrical shape and, additionally or alternatively, may have astepped, tapered, conical, or other shape that is generally dimensionedin accordance with the shape of the tapered end 120 of thecylindroconical profile of trocar 122 to permit the flow of coolant tomore effectively reach the distal regions of trocar 122. Additionally oralternatively, cooling chamber may have a square, hexagonal, or anysuitable shape. Additionally, the dielectric properties of sterile wateror saline flowing through cooling chamber 148 may enhance the overallablation pattern of antenna 100.

A coolant inflow tube 126 is in operable fluid communication at aproximal end thereof with a source of cooling fluid (not explicitlyshown), and, at a distal end thereof, coolant inflow tube 126 is influid communication with cooling chamber 146 to provide coolant thereto.Coolant inflow tube 126 may be formed from any suitable material, e.g.,a polymeric material, such as without limitation, polyimide. In anembodiment, coolant inflow tube 126 passes through coolant inflow port131. In some embodiments, a coolant outflow channel 136 may be providedto facilitate removal of coolant from cooling chamber 146, throughantenna assembly 100, to a collection reservoir (not explicitly shown).The coolant may be any suitable fluid, such as without limitation water,sterile water, deionized water, and/or saline.

Threaded section 145 of trocar 122 is configured to receive trocar screw144. Trocar screw 144 includes at the proximal end thereof an opening143 defined therein that is configured to accept the distal end of innercoaxial conductor 150. In embodiments, distal end of inner coaxialconductor 150 is fixed within opening 143 by any suitable manner ofelectromechanical attachment, such as without limitation welding,brazing, and/or crimping. As seen in FIG. 4A, an inflow groove 147 andan outflow groove 149 are disposed longitudinally through the threadedportion of trocar screw 144 to respectively facilitate the flow ofcoolant into, and out of, cooling chamber 148. Inflow groove 147 andoutflow groove 149 may be configured to accommodate the insertion ofcoolant inflow tube 126 and/or a corresponding outflow tube (notexplicitly shown). A return path 156 in the antenna assembly mayadditionally or alternatively provide an exit conduit for the coolingfluid.

In the illustrated embodiment, trocar 122 and proximal antenna member128 include a dielectric coating 121, 127, respectively, on therespective outer surfaces thereof. The dielectric coating 121, 127 mayinclude any suitable dielectric material, such as without limitation,ceramic material. In some embodiments, dielectric coating 121, 127 maybe formed from titanium dioxide and/or zirconium dioxide. Dielectriccoating 121, 127 may be applied to trocar 122 and/or proximal antennamember 128 by any suitable process, for example without limitation,plasma spraying or flame spraying. In embodiments, dielectric coating121, 127 has a thickness in the range of about 0.005 inches to about0.015 inches. During an ablation procedure, the dielectric coating 121,127 may provide improved dielectric matching and/or improved dielectricbuffering between the antenna and tissue, which may enable the use ofhigher power levels, which, in turn, may enable a surgeon to achievegreater ablation rates resulting in increased ablation size, reducedoperative times, and/or improved operative outcomes.

An outer jacket 124 is disposed about the outer cylindrical surface ofantenna assembly 100, e.g., the distal radiating portion 105, puck 130,and proximal radiating section 140. Outer jacket 124 may be formed fromany suitable material, including without limitation polymeric or ceramicmaterials. In some embodiments, outer jacket 124 is formed from PTFE.Outer jacket 124 may be applied to antenna assembly 100 by any suitablemanner, including without limitation, heat shrinking.

Continuing with reference to FIGS. 4A-4D, a method of manufacturingantenna assembly 100 is disclosed wherein inner coaxial conductor 150 isinserted into opening 143 of trocar screw 144. Inner coaxial conductor150 is electrically fixed to trocar screw 144 by any suitable manner ofbonding, such as without limitation, laser welding, brazing, orcrimping. The coaxial transmission line 138 and trocar screw 144subassembly is placed in a mold (not explicitly shown), such as withoutlimitation an injection micro-mold, that is configured to overmold thepuck 130. Advantageously, inflow groove 147 and outflow groove 149 arealigned with mold features (not explicitly shown) corresponding tocoolant inflow port 131 and coolant outflow port 133 such that, whenmolded, a continuous fluid connection is formed between inflow groove147 and coolant inflow port 131, and between outflow groove 149 andoutflow port 133.

Puck material e.g., ceramic; polyether block amide, available under thetradename PEBAX® from Arkema of Puteaux, France; polyetherimide,available under the tradename ULTEM® from Sabic Innovative Plastics IPB.V. of Bergen Op Zoom, Netherlands; polyimide-based polymer availableunder the tradename VESPEL® from E.I. Du Pont De Nemours and Company ofWilmington, Del., or any suitable polymer having dielectric properties,is shot into the mold, allowed to cool/and or set, and subsequentlyreleased from the mold to form an assembly that includes puck 130,trocar screw 144 and coaxial transmission line 138 as best illustratedin FIG. 4B. The formed puck 130 includes a center section 137 having anouter diameter corresponding to the outer diameters of trocar 122(inclusive of the thickness of dielectric coating 121) and/or proximalantenna member 128 (inclusive of the thickness of dielectric coating127). Puck 130 further includes a distal shoulder 141 having an outerdiameter corresponding to the inner diameter of trocar 122, and aproximal shoulder 139 having an outer diameter corresponding to theinner diameter of proximal antenna member 128.

Trocar 122 may then be threaded onto trocar screw 144 to form the distalradiating section 120, as best shown in FIG. 4C. Inflow tube 126 maythen be inserted into coolant inflow port 131. Proximal antenna member128 may then be positioned against puck 130 such that the distal end ofproximal antenna member 128 engages the proximal shoulder of puck 130,thus forming a sealed proximal radiation section 140.

Tension may be applied to inner coaxial conductor 150 and/or dielectric132 in a proximal direction, thereby drawing together distal radiatingsection 105, puck 130, and proximal radiating section 140, and placingpuck 130 in a state of compression. Inner coaxial conductor 150 and/ordielectric 132 may be fixed in a state of tension at an anchor point151, by any suitable manner of fixation, including without limitationspot welding, brazing, adhesive, and/or crimping. In this manner, theantenna sections are “locked” together by the tensile force of innercoaxial conductor 150 and/or dielectric 132, which may result inimproved strength and stiffness of the antenna assembly.

Outer jacket 124 may be applied to the outer surface of radiatingportion 12 by any suitable method, for example without limitation, heatshrinking, overmolding, coating, spraying, dipping, powder coating,baking and/or film deposition.

It is contemplated that the steps of a method in accordance with thepresent disclosure can be performed in a different ordering than theordering provided herein.

FIG. 5 is a schematic illustration of a microwave system, generallyshown as system 500, according to an embodiment of the presentdisclosure. Antenna 510 is used to ablate tissue on patient “P”. Antenna510 is coupled to coax cable 520 which has a center conductor 522 and anouter sheath 524. Outer sheath 524 is coupled to the ground terminal ofmicrowave generator 530 which includes a microwave source 535. Outersheath 524 is also coupled to RF generator 540 via a transmission line526. RF generator 540 includes an RF source 542 and sensors 544.Diplexer 550 is coupled between center conductor 522 and RF generator540. Microwave generator 530, RF generator 540 and diplexer 550 may beprovided as separate units or provided in generator 28 as shown in FIG.1.

RF generator 540 outputs RF energy to the diplexer 550 which combinesthe RF energy with the microwave energy outputted by microwave generator530. Diplexer 550 implements frequency domain multiplexing where twoports are multiplexed onto a third port. The diplexer 550 blocks the RFenergy from getting into the microwave generator 530 and blocksmicrowave energy from getting into the RF generator 540. Diplexer 550allows both the RF energy and the microwave energy to flow to antenna510 simultaneously through center conductor 522. The RF energy isoutputted from the antenna to the ablation zone 610 as depicted in FIG.6. The RF path is depicted by lines 620 in FIG. 5B. The RF energy flowsfrom antenna 510 to the ablation zone 610 and uses the same return pathas the microwave energy by utilizing the outer sheath 524.

The RF energy returning from the ablation zone is used as a feedbacksignal and is provided to the RF generator 540 via transmission line526. The return RF energy is combined with the RF energy provided by theRF source 542. The combined RF energy is then provided to sensors 544which measure the voltage, current and phase of the RF energy. A sensormay be operable to measure at least one parameter of the second energygenerated by the second energy source and the second energy returnedfrom the region of tissue. Such sensors are within the purview of thoseskilled in the art. The measured voltage, current, and/or the phase ofthe RF energy, is provided to a controller 560 which calculates thetissue impedance based on the measured voltage and current. Based on thetissue impedance, the controller 560 controls the output of themicrowave generator 530. Alternatively, the controller 560 can calculatethe tissue impedance and display the value on a display (not shown) sothat a user may control the output of the microwave generator 530 or thecontroller 560 can automatically adjust the output of the microwavegenerator by comparing the calculated tissue impedance to apredetermined impedance stored in the controller.

The controller 560 may include a microcontroller operably connected to amemory, which may be volatile type memory (e.g., RAM) and/ornon-volatile type memory (e.g., flash media, disk media, etc.). Themicrocontroller includes an output port that is operably connected tothe microwave generator 530 allowing the microcontroller to control theoutput of the microwave generator 530. Those skilled in the art willappreciate that the microcontroller may be substituted by any logiccontroller (e.g., control circuit) adapted to perform the calculationsdiscussed herein

In another embodiment according to the present disclosure, and as shownin FIG. 7, an electrosurgical system 700 is provided with an RF returnpad 710 to receive a return RF signal from the ablation zone 810 asshown in FIG. 8. As shown in FIG. 8, the antenna 510 outputs RF energyin a path indicated by 820. The outputted RF energy is received by theRF return pad 810 and provided as a feedback to the RF generator 540which is used to directly or indirectly control the microwave generator530. The RF return pad 710 may have any suitable regular or irregularshape such as circular or polygonal. RF return pad 710 may be aconductive pad that may include a plurality of conductive arranged in aregular or irregular array. Each of the plurality of conductive elementsmay be equally-sized or differently-sized and may form a grid/array onthe conductive pad. The plurality of conductive elements may also bearranged in a suitable spiral or radial orientation on the conductivepad. The use of the term “conductive pad” as described herein is notmeant to be limiting and may indicate a variety of different padsincluding, but not limited to, conductive, inductive, or capacitivepads.

Although the above described embodiments describe a generator 28 havingthe microwave generator 530, RF generator 540, diverter 550 andcontroller 560, it is to be appreciated by one skilled in the art thatsome or all of these elements may be included in a single device or mayfunction as separate components that are interconnected when used duringan ablation procedure. Further, controller 560 may be included in thegenerator 28 or it may be a separate computer or laptop connected to thegenerator 28.

The described embodiments of the present disclosure are intended to beillustrative rather than restrictive, and are not intended to representevery embodiment of the present disclosure. Various modifications andvariations can be made without departing from the spirit or scope of thedisclosure as set forth in the following claims both literally and inequivalents recognized in law.

1-12. (canceled)
 13. A method for controlling a microwave generator, themethod comprising: generating first energy at a first frequency at afirst energy source; generating second energy at a second frequency at asecond energy source; multiplexing the first and second energies tooutput multiplexed energy; transmitting the multiplexed energy to aload; receiving the second energy from the load; measuring a parameterof the second energy; and controlling the first energy source based onthe measured parameter of the second energy.
 14. The method according toclaim 13, wherein the first frequency is higher than the secondfrequency.
 15. The method according to claim 14, wherein the firstenergy source is a microwave generator and the second energy source is aradio frequency generator.
 16. The method according to claim 13, furthercomprising calculating an impedance of the load based on the measuredparameter of the second energy.
 17. The method according to claim 16,further comprising controlling the first energy source based theimpedance of the load.
 18. The method according to claim 13, wherein themeasured parameter of the second energy is at least one of voltage orcurrent.
 19. The method according to claim 13, wherein multiplexing thefirst and second energies to output multiplexed energy includesoutputting the first energy and the second energy simultaneously whileblocking the first energy from the second energy source and blocking thesecond energy signal from the first energy source.
 20. The methodaccording to claim 13, wherein receiving the second energy from the loadincludes providing a return path for the second energy to the secondenergy source.
 21. A method for controlling an electrosurgical energysource, the method comprising: generating a first electrosurgical energysignal at a first frequency from a first electrosurgical energy source;generating a second electrosurgical energy signal at a second frequencyfrom a second electrosurgical energy source; outputting the first andsecond electrosurgical energy signals simultaneously as a multiplexedsignal while blocking the first electrosurgical energy signal from thesecond electrosurgical energy source and blocking the secondelectrosurgical energy signal from the first electrosurgical energysource; and controlling the first electrosurgical energy source based ona measured parameter of the second electrosurgical energy signal. 22.The method according to claim 21, further comprising transmitting themultiplexed signal to a load.
 23. The method according to claim 22,further comprising receiving, at the second electrosurgical energysource, the second electrosurgical energy signal from the load.
 24. Themethod according to claim 23, wherein receiving, at the secondelectrosurgical energy source, the second electrosurgical energy signalfrom the load includes providing a return path for the secondelectrosurgical energy signal to the second electrosurgical energysource.
 25. The method according to claim 22, further comprisingdetermining an impedance of the load based on the measured parameter ofthe second electrosurgical energy signal.
 26. The method according toclaim 25, further comprising controlling the first electrosurgicalenergy source based the impedance of the load.
 27. The method accordingto claim 21, wherein the measured parameter of the secondelectrosurgical energy signal is at least one of voltage or current. 28.The method according to claim 21, wherein the first frequency is higherthan the second frequency.
 29. The method according to claim 21, whereinthe first electrosurgical energy source is a microwave generator and thesecond electrosurgical energy source is a radio frequency generator. 30.A method for controlling an electrosurgical energy source, the methodcomprising: generating a first electrosurgical energy signal at a firstfrequency from a first electrosurgical energy source; generating asecond electrosurgical energy signal at a second frequency from a secondelectrosurgical energy source; transmitting the first and secondelectrosurgical energy signals simultaneously as a multiplexed signal toa load while blocking the first electrosurgical energy signal from thesecond electrosurgical energy source and blocking the secondelectrosurgical energy signal from the first electrosurgical energysource; and controlling the first electrosurgical energy source based onan impedance of the load.
 31. The method according to claim 30, whereinthe first electrosurgical energy source is a microwave generator and thesecond electrosurgical energy source is a radio frequency generator. 32.The method according to claim 30, further comprising receiving thesecond electrosurgical energy signal from the load at the secondelectrosurgical energy source.